|Publication number||US7927010 B2|
|Application number||US 11/780,685|
|Publication date||Apr 19, 2011|
|Filing date||Jul 20, 2007|
|Priority date||Dec 5, 2005|
|Also published as||CA2630795A1, CA2630795C, EP1957966A2, US7788047, US7857506, US8506162, US20070126794, US20070255527, US20090134882, US20090180513, WO2007067881A2, WO2007067881A3|
|Publication number||11780685, 780685, US 7927010 B2, US 7927010B2, US-B2-7927010, US7927010 B2, US7927010B2|
|Inventors||Karl G. Schick, David Uhen|
|Original Assignee||SenCal, LLC|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (56), Non-Patent Citations (6), Referenced by (6), Classifications (14), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The invention generally relates to disposable, pre-sterilized, pre-calibrated, in-line sensors. More specifically, the invention relates to disposable, pre-calibrated, pre-validated probes or sensors that contain non-volatile memory capable of storing specific conductivity and preferably also information concerning the “out-of-box” performance of the probe or sensor.
Pre-sterilized, single-use bag manifolds such as those used in bio-pharmaceutical production (see U.S. Pat. No. 6,712,963, incorporated here by reference) lack the ability to monitor and validate important, analytical solution parameters during the processing of biopharmaceutical solutions. The use of such bag manifolds, for example, in preparative chromatography or tangential flow filtration (TFF) or fluid transfer generally, is severely limited by the general lack of pre-sterilized, pre-calibrated, pre-validated in-line sensors and detectors
In-line, flow through-type sensors and detectors are well known in industry and are extensively used in analytical laboratories, pilot plants and production facilities. In-line conductivity detectors, in particular, are used in ion chromatography, preparative chromatography, flow injection analysis (FIA), tangential flow filtration (TFF), as well as water purity analysis. However, prior-art in-line flow through conductivity sensors and detectors are typically made out of machined, stainless steel or plastic materials. These sensors and detectors are intended for permanent installations and long-term use. Prior-art in-line sensors and detectors are difficult to sterilize, require in-field calibration and validation by an experienced operator before use, and are very expensive, often costing thousands of dollars. Consequently, prior art sensors and detectors are not suited for a single-use sensor application.
The use of a memory device imbedded in disposable clinical sensors has been reported. For example, U.S. Pat. No. 5,384,028 deals with the fabrication of an enzyme-based glucose biosensor that utilizes a sensor-imbedded data memory device. However, this patent utilizes the memory device for purposes of sensor traceability and inventory control. Furthermore, this patent requires sensor calibration and/or validation by the clinician immediately prior to each use.
In line sensors for use in bioprocessing applications must be designed to meet government regulations regarding device traceability and validation. In addition, in-line sensors must meet the application requirements for accuracy and precision. These requirements present extra challenges and pose unique problems when the in-line sensor is to be disposable and suitable for single use as desired. Another problem is how to provide disposable in-line sensors that are pre-calibrated. Also for aseptic sensor applications, each single-use sensor, must meet sterilization requirements. Furthermore, single-use sensors must meet economic requirements, i.e. sensors must be low cost, easy to replace with negligible disposal expense.
The present invention overcomes the aforementioned shortcomings and problems faced by the industry by providing a low-cost, pre-sterilized, pre-calibrated, in-line sensor capable of being traced and validated. The invention further provides a sensor-embedded, non-volatile memory chip capable of storing device-specific information for instant recall by the user.
The preferred embodiment is an in-line conductivity sensor system used to measure the conductivity of the process flow solution. The present embodiment has two main components: the user interface and the sensor assembly module.
The sensor assembly module contains a short tubular fluid conduit, one or more sensor or probe components, referred to herein at times as a sensor or a sensor component. The sensor assembly module further includes a printed circuit board (PCB) with a sensor-embedded non-volatile memory chip. Sensor components can include electrodes, toroidal sensors or other arrangements. All components are designed or selected for highly automated production methods such as those used in surface mounted electronic assemblies. The present disclosure focuses on multiple electrode arrangements as the preferred embodiment for carrying out the sensing function.
In the illustrated preferred embodiment, four electrodes are press-fitted into and through four, linearly arranged holes in the fluid conduit wall. The electrodes are epoxied, cemented or sealed into place to prevent leaks or contamination. The electrodes are connected to a PCB. The PCB contains a thermistor, in thermal contact with two of the conductivity electrode pins. The PCB also contains a non-volatile memory chip or EEPROM, which is used to store sensor-specific information, which typically includes the sensor's ID number, a Cell Constant, a Temperature Offset Value and the calibration date.
Furthermore, each sensor has an “out-of-box” performance variance value which is also stored in the non-volatile memory chip. This “out-of-box” value is a statistically derived performance variance (measured for example in 0.100 molar KCl at 25.0° C.) that represents the maximum measurement error for that specific sensor within a 98% confidence limit. The statistically derived variance value is based on the performance analysis of all calibrated sensors within a production run, typically of between about 100 and about 500 sensors. The factory determined performance variance represents a predictive, “out-of-box” sensor performance level.
The user interface performs the conductivity measurement by monitoring the current across the two inner working electrodes. Prior to the conductivity measurement, the user interface retrieves the Cell Constant from the sensor memory. The measured solution conductance is multiplied by the Cell Constant to arrive at the actual conductivity of the tested process solution. The sensor-specific Cell Constant is determined during factory calibration using a solution (for example 0.100 molar KCl at 25.0° C.) with a known conductivity. The Cell Constant is subsequently stored in the non-volatile memory of the sensor assembly module.
It is a general aspect or object of the present invention to provide a disposable conductivity sensor.
Another aspect or object of the present invention is to provide a disposable sensor suitable for one-time use, which may be integrated with other disposable equipment, including bag manifolds, employed in the separation and purification of fluids, that are suitable for single-use applications.
An aspect or object of the present invention is to reduce the cost associated with the construction of conductivity sensors.
Another aspect or object of the present invention is to provide a sensor having a stored “out-of-box” performance variance value.
These and other objects, aspects, features, improvements and advantages of the present invention will be clearly understood through a consideration of the following detailed description.
As required, detailed embodiments of the present invention are disclosed herein; however, it is to be understood that the disclosed embodiments are merely exemplary of the invention, which may be embodied in various forms. Therefore, specific details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the present invention in virtually any appropriate manner.
A system designed to measure the conductivity of fluids in a closed fluid system by using a pre-calibrated disposable in-line electrical conductivity sensor is shown in
Leads such as the illustrated electrical connecting wires 110 connect the conductivity sensor 108 to a conductivity readout device or user interface 112. The user interface, generally designated as 112, communicates with the sensor 108 and measures conductivity by sending and receiving both digital and analog electrical signals along the leads 110. The user interface 112 has a display 114 to display information, for example, the conductivity reading, the temperature reading, and information stored on the conductivity sensor 108 relating to the calibration, validation and tracking of the sensor.
The fluid conduit 102 traverses the assembly 100 such as along its width as illustrated. Electrodes 204 are in electrical communication with the interior of the fluid conduit 102. In the illustrated embodiment, the fluid conduit is intersected by four electrodes of the conductivity sensor 108. These electrodes 204 can be positioned along the interior of the conduit 102, such as at the middle portion of the conduit. Gold-plated electrodes can be used such as ones that are about 1 mm to about 2 mm in diameter or between about 0.025 inches to 0.05 inches in diameter. Such electrodes preferably are arranged in-line approximately 2 to 2.5 mm (about 0.08 inch to 0.10 inch) apart.
In the illustrated embodiment, the electrode pins 204 are press-fitted into and through four linearly arranged holes in the wall of the fluid conduit 102 and extend into the hollow interior of the fluid conduit 102. Typical protrusion into the conduit is on the order of about 3 mm to about 13 mm (about ⅛ inch to about 0.5 inch). The electrodes 204 are epoxied, cemented or otherwise sealed to the wall of the fluid conduit 102 to prevent leaks or contamination. Additionally, the electrodes 204 are in electrical communication with their respective traces on the sensor 108.
In other embodiments, the electrodes 204 may only have two electrodes or pins rather than four of the preferred embodiment. In addition, the electrodes may be constructed from other materials, such as stainless steel wire, titanium wire, or any other non-corrosive material. Disposability is a criteria to be considered in selecting these or any other materials of the device.
Opposite the electrodes 204, the PCB 306 is wedged between two rows of five pins of a miniature, 8-pin DIN connector 308. These five pins of the DIN connector 308 are in direct contact with the PCB 306 and are soldered to the PCB 306. The three remaining pins of the DIN connector 308 are wired and soldered to the PCB 306. The end of the sensor 108 is capped and sealed by the cap-ring 310. The DIN connector 308 is detachably connected to the user interface 112 by the connecting wires 110. Each pin of the DIN connector 308 is associated with an individual wire of the connecting wires 110.
A sensor-embedded non-volatile memory chip or an EEPROM 404 is mounted on the surface of the PCB 304. The non-volatile memory chip or EEPROM 404 is used to store sensor-specific information. This information can be called up, displayed and printed out, on demand, by the user interface 112.
The PCB 306 also contains a surface-mounted capacitor 406 that is visible in
The non-volatile memory chip (or EEPROM) 404 uses the bi-direction serial data line 602 and a serial clock line 604 to communicate with the user interface. Different non-volatile memory chips or EEPROMS have different protocols, which are known in the art. In this embodiment, the serial data and serial clock lines allow a user interface 112 or a calibration device to read, erase, and write data to the non-volatile memory chip 404. The serial data line 602 is an open drain terminal. Therefore, the serial data line requires a pull-up resistor 606 connected to the voltage source coming from the DIN connector 308. The in this embodiment, the thermistor 402 also serves as the pull-up resistor 606.
The sensor-specific information is electronically entered into the non-volatile memory chip 404 during factory calibration of the conductivity sensor 108. The sensor-specific information may include the following: Cell Constant (K), Temperature Offset, the unique Device ID, and the Calibration Date, the production lot number of the sensor, the production date of the sensor, the type of fluid used for calibration, the actual temperature of the fluid used, and “out-of-box” sensor performance value.
During production, small differentiations in the electrodes 104, the respective angles of the electrodes, and the gaps between the individual electrodes will result in different conductivity readings for each sensor produced. These differences can significantly affect accuracy. In keeping with the invention, these differences are successfully addressed by having each sensor normalized or calibrated as a part of its manufacturing procedure.
In the illustrated example, each conductivity sensor 108 is calibrated using certified 0.100 molar KCl (potassium chloride) solution maintained at 25.0° C. The conductance, which is dependent on the cell geometry and the solution resistivity, is determined by measuring the voltage drop across the electrodes. The measured conductance together with known solution conductivity allows the calculation of the sensor-specific Cell Constant (K). The Cell Constant (K) is determined by the following equation:
ti [Solution Conductivity,(S/cm)]/[Conductance (S)]=[Cell Constant, K,(cm−1)]
The sensor-specific Cell Constant (K) is then stored in the non-volatile memory 404 of the conductivity sensor 108.
For example, the solution conductivity for a 0.100 molar KCl solution is known to be 12,850 μS (or 0.01285 S) at 25.0° C. The typical measured conductance for a 0.100 molar KCl solution using a sensor with a ⅛ inch Luer conductivity cell with a 0.10 inch electrode separation is 0.0379 Siemens. Using the equation above, the corresponding Cell Constant (K) for the particular disposable sensor of this illustration is calculated to be 0.339 cm−1.
Once the Cell Constant (K) is calculated it is stored on the sensor. The user interface will recall the Cell Constant (K) from the sensor. When undergoing normal operations, the user interface 112 measures the conductance in Siemens of the solution flowing through the fluid conduit 102 by passing a current through the electrodes 204 and measuring the current across the two inner electrodes 204. The user interface 112 will then use the Cell Constant (K) for this particular disposable sensor to determine the conductivity of the solution flowing through the fluid conduit. The user interface calculates the solution's conductivity by multiplying the measured conductance by the Cell Constant (K), as demonstrated in the following equation:
[Cell Constant, K,(cm−1)]×[Conductance (S)]=[Solution Conductivity,(S/cm)]
The sensor, once calibrated, provides a linear response for NIST traceable standard solutions ranging from 1 to 200,000 μS.
The temperature of a solution will also affect its conductivity. As a result, the sensor must also measure and account for the temperature of the solution to achieve an accurate conductivity measurement. Ordinarily, un-calibrated thermistors will have a variance of ±5% between their measured reading and the actual temperature. A calibrated thermistor may achieve a variance of ±1% or less.
In this regard, a sensor-specific Temperature Offset is calibrated at the factory. To determine the Temperature Offset, temperature readings are made while a 25.0° C. KCl solution is pumped through the fluid conduit and over the electrodes. A comparison is then made between the temperature reading of the un-calibrated thermistor on the sensor (Tsen) with that of a NIST-traceable thermometer or thermistor (Tref). The difference between the two readings is the Temperature Offset (Tref−Tsen=TempOffset). The Temperature Offset may have either a positive or a negative value. The sensor-specific Temperature Offset is then stored in the non-volatile memory on the sensor.
Each sensor has an “out-of-box” performance variance value which is also stored on the sensor, typically in the non-volatile memory chip. This “out-of-box” value is a statistically derived performance variance (measured in 0.100 molar KCl at 25.0° C.) that represents the maximum measurement error for that specific sensor within a 98% confidence limit. The statistically derived variance value is based on the performance analysis of all calibrated sensors within a production run, typically of between about 100 and about 500 sensor assemblies. The factory determined performance variance represents a predictive, “out-of-box” sensor performance level. This statistical treatment is analogous to and representative of a sensor validation procedure. Factory pre-validated conductivity sensors are thereby provided. The meaning of “pre-validated” is further illustrated herein, including as follows.
In the preferred embodiment, each conductivity sensor undergoes two factory measurements. The first measurement involves sensor calibration and determination of the specific Cell Constant (i.e. response factor) using a 0.100 molar KCl solution at 25.0° C. as described herein. In another separate and distinct measurement with 0.100 molar KCl solution at 25.0° C., the solution conductivity is experimentally determined using the pre-calibrated sensor. When taking into account the experimentally derived solution conductivities for all pre-calibrated sensors, the mean conductivity value closely centers around the theoretical value of 12,850 μS with a 3-sigma standard deviation of +/−190 μS or +/−1.5% An operator may access this information via the user interface 112 or Conductivity Monitor.
In addition to the calibration information, such as the Cell Constant (K) and the Temperature Offset, the sensor-specific Device ID, Calibration Date, and statistical information are store in the non-volatile memory. The Device ID is stored as a string of numbers, for example: nn-ss-xxxx-mmyy. In this example, the variables represent the sensor lot number (nn), fluid conduit size (ss), the device serial number (xxxx) and the manufacturing date by month and year (mmyy). For example, sensor containing the Device ID of 02-02-0122-1105 means that this sensor was the 122nd sensor made in lot 02 of conduit size 02 (a fluid conduit with a diameter of ⅜″ or 9.5 mm having a barb connector), manufactured in November of 2005. In this illustration, the sensor-specific Calibration Date or the date on which the sensor was calibrated using 0.100 molar KCl solution at 25.0° C. is also stored in the sensor's non-volatile memory as a separate data entry.
Additionally, statistical information or statistical data about the entire lot may also be stored in the non-volatile memory. For example, the average cell constant for lot 122 may be stored in the non-volatile memory of each sensor in lot 122. The standard deviation for cell constants for each lot may also be stored (i.e. “out-of-box” variance value) in the non-volatile memory of each sensor produced in that lot. This allows the user to determine whether a particular sensor is within the statistical range to achieve the proper margin of error for a specific experiment or bio-processing operation. As those skilled in the art will appreciate, other known statistical methods may be utilized, the results of which may be stored in the non-volatile memory on the sensing device.
In addition to storing the Cell Constant (K), Temperature Offset, Device ID, the Calibration Date, and other information in the non-volatile memory on the sensor, a summary of this information may be printed on the outside of the sensor. This information may be consulted by the user, used to later re-calibrate the sensor, and allows the user to input the printed information directly into the user interface.
It will be understood that the embodiments of the present invention which have been described are illustrative of some of the applications of the principles of the present invention. Numerous modifications may be made by those skilled in the art without departing from the true spirit and scope of the invention.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3447070 *||Apr 11, 1966||May 27, 1969||Exxon Research Engineering Co||Apparatus for measuring the electrical conductivity of corrosive fluids|
|US4147596||Dec 30, 1977||Apr 3, 1979||Texas Instruments Incorporated||Method and apparatus for monitoring the effectiveness of corrosion inhibition of coolant fluid|
|US4227151||Aug 28, 1978||Oct 7, 1980||Malcom-Ellis (Liverpool) Limited||Measurement and monitoring of the electrical conductivity of liquor samples|
|US4303887 *||Oct 29, 1979||Dec 1, 1981||United States Surgical Corporation||Electrical liquid conductivity measuring system|
|US4513248 *||Feb 1, 1983||Apr 23, 1985||Conax Corporation||Fluid conductivity sensor|
|US4740755||May 30, 1986||Apr 26, 1988||Cobe Laboratories, Inc.||Remote conductivity sensor having transformer coupling in fluid flow path|
|US5231867||Jul 3, 1991||Aug 3, 1993||Dipl.-Ing. Wrede & Niedecken Verwaltung Gmbh||Device for detecting leaks in a flanged joint|
|US5384028||Aug 27, 1993||Jan 24, 1995||Nec Corporation||Biosensor with a data memory|
|US5421983||Nov 12, 1993||Jun 6, 1995||E. I. Du Pont De Nemours And Company||Anion selective electrodes containing fumed silica|
|US5435170 *||Dec 30, 1993||Jul 25, 1995||Voelker; Paul J.||Method and apparatus for fluid quality sensing|
|US5455513 *||Dec 7, 1993||Oct 3, 1995||Falmouth Scientific, Inc.||System for measuring properties of materials|
|US5686309 *||Jan 19, 1996||Nov 11, 1997||Coulter International Corp.||Method and apparatus for determination of hemoglobin content of individual red blood cells|
|US5821399||Jul 16, 1993||Oct 13, 1998||I-Stat Corporation||Automatic test parameters compensation of a real time fluid analysis sensing device|
|US5869971 *||May 17, 1996||Feb 9, 1999||Sendx Medical, Inc.||Method and apparatus for ratiometric measurement of hematocrit|
|US6173600||Jan 4, 1999||Jan 16, 2001||Tao Electronics Ltd.||Measuring instrument with memory|
|US6259242 *||May 26, 1999||Jul 10, 2001||Coulter International Corp.||Apparatus incorporating a sensing conduit in conductive material and method of use thereof for sensing and characterizing particles|
|US6275717||Jun 23, 1998||Aug 14, 2001||Elan Corporation, Plc||Device and method of calibrating and testing a sensor for in vivo measurement of an analyte|
|US6350382||Jun 23, 2000||Feb 26, 2002||Scilog, Inc.||Enhancing filtration yields in tangential flow filtration|
|US6404204||May 1, 2000||Jun 11, 2002||ARETé ASSOCIATES||Sensor and sensor system for liquid conductivity, temperature and depth|
|US6426629 *||Jan 13, 1997||Jul 30, 2002||Gambro Ab||Method and apparatus for measuring an electrical parameter of a fluid|
|US6607669||Oct 15, 2001||Aug 19, 2003||Scilog, Inc.||Method and apparatus for enhancing filtration yields in tangential flow filtration|
|US6614212 *||Sep 10, 2002||Sep 2, 2003||Gambro, Inc.||Differential conductivity hemodynamic monitor|
|US6623698||Mar 12, 2001||Sep 23, 2003||Youti Kuo||Saliva-monitoring biosensor electrical toothbrush|
|US6650933||Apr 7, 2000||Nov 18, 2003||Anatoly Ivanovich Obabkov||Method for the express diagnosis of the physiological condition of a biological object and device for realizing the same|
|US6664793 *||Mar 1, 2002||Dec 16, 2003||Allen R. Sampson||Fluid presence and qualitative measurements by transient immitivity response|
|US6673622 *||Jan 15, 1999||Jan 6, 2004||Hemosense, Inc.||Coagulation or lysis assays by measuring impedance|
|US6683464||Mar 1, 2002||Jan 27, 2004||Kavlico Corporation||Stabilized conductivity sensing system|
|US6712963||Jun 14, 2002||Mar 30, 2004||Scilog, Llc||Single-use manifold for automated, aseptic transfer of solutions in bioprocessing applications|
|US6799883||Dec 20, 1999||Oct 5, 2004||Air Liquide America L.P.||Method for continuously blending chemical solutions|
|US6812709||May 9, 2003||Nov 2, 2004||Endress + Hauser Conducta Gesellschaft für Mess- und Regeltechnik mbH + Co.||Sensor for measuring the electrical conductivity of a fluid medium|
|US6828808||Jul 10, 2001||Dec 7, 2004||The Johns Hopkins University||Long-life conductivity sensor system and method for using same|
|US6834258 *||Dec 31, 2002||Dec 21, 2004||Rosemount, Inc.||Field transmitter with diagnostic self-test mode|
|US6930486||Aug 7, 2003||Aug 16, 2005||Pulsafeeder, Inc.||Conductivity sensor|
|US7287699 *||Aug 5, 2005||Oct 30, 2007||Honeywell International Inc.||Sensor calibration method and systems|
|US7523649||Nov 26, 2004||Apr 28, 2009||Separation Technology, Inc.||Method and apparatus for ultrasonic determination of hematocrit and hemoglobin concentrations|
|US7733097 *||Sep 6, 2005||Jun 8, 2010||Emz-Hanauer Gmbh & Co. Kgaa||Method for determining a property of a fluid for a household device|
|US20030020494||May 17, 2002||Jan 30, 2003||Isabelle Desmier||Fuel sensor|
|US20030145646||Feb 6, 2002||Aug 7, 2003||Henry Kent D.||Multi-parameter monitoring system|
|US20040014233||Jan 31, 2002||Jan 22, 2004||University Of Massachusetts Massachusetts Corporation||Thermal analysis for detection and identification of explosives and other controlled substances|
|US20040017201 *||Jul 29, 2003||Jan 29, 2004||Brugger James M.||Differential fluid parameter determination|
|US20040155066||Jan 26, 2004||Aug 12, 2004||Schick Karl G.||Single-use manifold for automated, aseptic transfer of soulutions in bioprocessing applications|
|US20040170530||Mar 11, 2004||Sep 2, 2004||Prometheus Biosciences, Inc.||Systems and methods for monitoring chemical and biological activities using differential measurements|
|US20050145020||Feb 8, 2005||Jul 7, 2005||Vijay Mathur||Modular film sensors with record memory for a modular automated diagnostic apparatus|
|US20050189936||Feb 25, 2005||Sep 1, 2005||Quackenbush John K.||Removable breaking calibration connector for toroidal conductivity sensor and method of calibration|
|US20050255491||Nov 15, 2004||Nov 17, 2005||Lee Frank D||Small molecule and peptide arrays and uses thereof|
|US20060014212||Feb 25, 2005||Jan 19, 2006||Epitome Biosystems, Inc.||Proteome epitope tags and methods of use thereof in protein modification analysis|
|US20060042964||Oct 27, 2005||Mar 2, 2006||Sohrab Mansouri||Automated system for continuously and automatically calibrating electrochemical sensors|
|US20090180513 *||Jul 16, 2009||Sencal Llc||Disposable, pre-calibrated, pre-validated sensors for use in bio-processing applications|
|US20100021993 *||Nov 20, 2007||Jan 28, 2010||Ge Healthcare Bio-Sciences Corp.||System for assembling and utilizing sensors in containers|
|USH2228 *||Dec 7, 2004||Jan 6, 2009||The United States Of America As Represented By The Secretary Of The Navy||Temperature compensated fluid conductivity piping measurement|
|DE19720504A1||May 16, 1997||Nov 19, 1998||Conducta Endress & Hauser||Apparatus for holding a measuring electrode|
|EP0654664A2||Oct 27, 1994||May 24, 1995||E.I. Du Pont De Nemours And Company||Monensin amides for sodium-selective electrodes|
|JPH1019835A||Title not available|
|JPS59160746A||Title not available|
|WO1992017775A1||Apr 2, 1992||Oct 15, 1992||Kodak Ltd||Electrode calibration|
|WO2000006761A1||Jul 29, 1998||Feb 10, 2000||Hemosense Inc||Method and device for measuring blood coagulation or lysis by viscosity changes|
|1||"Siemens (unit)", Wikipedia, http://en.wikipedia.org/wiki/Siemens-(unit), Oct. 5, 2009, USA.|
|2||"Siemens (unit)", Wikipedia, http://en.wikipedia.org/wiki/Siemens—(unit), Oct. 5, 2009, USA.|
|3||PCT/US2006/061561 International Search Report and Written Opinion, dated Jun. 4, 2007.|
|4||U.S. Appl. No. 11/294,296, filed Dec. 5, 2005, Schick.|
|5||U.S. Appl. No. 11/741,162, Apr. 27, 2007, Schick.|
|6||U.S. Appl. No. 12/407,553, filed Mar. 19, 2009, Schick.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US8175835||May 17, 2006||May 8, 2012||Honeywell International Inc.||Flow sensor with conditioning-coefficient memory|
|US8718981||May 9, 2011||May 6, 2014||Honeywell International Inc.||Modular sensor assembly including removable sensing module|
|US20070271070 *||May 17, 2006||Nov 22, 2007||Honeywell International Inc.||Flow sensor with conditioning-coefficient memory|
|WO2014039640A2||Sep 5, 2013||Mar 13, 2014||Parker-Hannifin Corporation||Risk-managed, single-use, pre-calibrated, pre-sterilized sensors for use in bio-processing applications|
|WO2014150832A2||Mar 12, 2014||Sep 25, 2014||Parker-Hannifin Corporation||Single-use sensors in bioreactors, biotech purification and bioprocessing|
|WO2015200269A1||Jun 23, 2015||Dec 30, 2015||Parker-Hannifin Corporation||Multiple identification point automated parameter assurance method|
|U.S. Classification||374/45, 73/335.05, 324/441, 374/147, 374/174, 324/439|
|International Classification||G01N25/58, G01N27/00|
|Cooperative Classification||A61M1/3669, A61M2205/6018, G01N27/10, A61M1/3621|
|European Classification||G01N27/10, A61M1/36C|
|Jul 15, 2013||AS||Assignment|
Owner name: SENCAL LLC, WISCONSIN
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SCHICK, KARL G.;UHEN, DAVID;REEL/FRAME:030799/0583
Effective date: 20051220
Effective date: 20120816
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:SENCAL LLC;REEL/FRAME:030797/0463
Owner name: PARKER-HANNIFIN CORPORATION, OHIO
|Jul 16, 2013||AS||Assignment|
Owner name: PARKER-HANNIFIN CORPORATION, OHIO
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:SENCAL, LLC;REEL/FRAME:030803/0490
Effective date: 20120809
|Oct 20, 2014||FPAY||Fee payment|
Year of fee payment: 4